US7276028B2 - Sensor in vivo measurement of osmotic changes - Google Patents
Sensor in vivo measurement of osmotic changes Download PDFInfo
- Publication number
- US7276028B2 US7276028B2 US10/559,323 US55932304A US7276028B2 US 7276028 B2 US7276028 B2 US 7276028B2 US 55932304 A US55932304 A US 55932304A US 7276028 B2 US7276028 B2 US 7276028B2
- Authority
- US
- United States
- Prior art keywords
- sensor
- pressure
- membranes
- membrane
- osmotic
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active, expires
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14546—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring analytes not otherwise provided for, e.g. ions, cytochromes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/07—Endoradiosondes
- A61B5/076—Permanent implantations
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
- A61B2560/02—Operational features
- A61B2560/0204—Operational features of power management
- A61B2560/0214—Operational features of power management of power generation or supply
- A61B2560/0219—Operational features of power management of power generation or supply of externally powered implanted units
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/02—Details of sensors specially adapted for in-vivo measurements
- A61B2562/028—Microscale sensors, e.g. electromechanical sensors [MEMS]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0031—Implanted circuitry
Definitions
- Porous etching (anodic oxidation) of silicon is also a well-known technique.
- Porous silicon (PS) is made by electrochemical etching of a silicon wafer in solutions containing hydrofluoric acid (HF).
- HF hydrofluoric acid
- HF is sold in an aqueous solution with up to 50% of HF.
- the first attempts to form porous silicon were performed using only HF diluted in de-ionised and ultra-pure water. Due to the hydrophobic character of the clean Si surface, absolute ethanol is usually added to the aqueous solution to increase the wettability of the PS surface. So far this technique is mainly used for making visible photoluminescence (PL).
- sol-gel techniques are well known processes, used for a variety of different commercial applications, ranging from optical and electrical coatings to improve the scratch resistance.
- the pressure sensors are based on a pressure sensor where the deflection of a pressure sensitive membrane is measured by the change in the electrical capacitance between this membrane (which doubles as an electrode) and a fixed electrode.
- This type of sensor excludes the use of a differential element as long as the medium where the measuring of the pressure is conducted, is conductive (as in the present case where water is used).
- the sensor element described in the U.S. Pat. No. 5,337,747 would not work according to its intentions. This is caused by the fact that more than 99% of the capacitance measured will be caused by the mounting between the membrane ( 10 ) and the other electrode ( 12 ) which is fixed and is not changing with changing pressure in the chamber. Less than 1% of the total capacitance will be modulated by the deflection of the pressure sensitive membrane.
- U.S. Pat. No. 6,224,550 by one of the present inventors, May 1, 2001, relies on maintaining a similar osmolality on both sides of an osmotic membrane. This is obtained by allowing water to flow freely through the membrane and thereby changing the volume (and thereby the concentration) of the “calibrated” fluid inside the sensor.
- One of the disadvantages with this design is the fact that a significant amount of water must be transported through the membrane when the osmolality in the body is changing.
- only limited fluxes are possible through such membranes, which means that a relatively large area of the osmotic membrane is needed.
- the time response will depend on the actual position of a piston, and as such, the sensor will also be non-linear.
- a more fundamental problem with this sensor is the fact that to obtain a “calibrated” fluid, the small electrolytes must be allowed to pass through the membrane. As glucose and larger molecules are excluded from passing through the membrane, the “calibrated” fluid will always have to maintain a higher concentration of the electrolytes (chlorine, potassium, etc). The result is an unstable element, from which the electrolytes gradually will be drained out, and in the end the calibrated fluid will disappear.
- osmosis is the transport of a solvent across a semipermeable membrane caused by differences in the concentration of solutes on either side of the membrane.
- Osmosis is a process where certain kinds of molecules in a liquid are preferentially blocked by a “semipermeable” membrane.
- the solvent in our case water
- the solvent is diffusing through the membrane into the more concentrated solution, more so than in the opposite direction.
- the result is a combination of two effects. One is that an osmotic (hydrostatic) pressure is built up in the volume of higher concentration. The other is the reduction in the concentration difference caused by the increased volume of solvent.
- Osmotic pressure is one example of a colligative property, that is a property which depends only on the number of solute molecules, and not on the nature of the molecules. For relatively small concentrations, as those observed in the body, the osmotic pressure is equal to the pressure that the solute molecules would exert given they were in a gas of the same concentration.
- V is the volume of solution containing one mole of solute.
- i is the “van't Hoff factor”, which is a measure of the relative increase in amount of entities (particles) due to dissociation.
- the present invention can be used to monitor the amount of medication.
- Measurement of glucose in ISF is becoming recognised as an alternative to measuring the glucose directly in the blood.
- the glucose measurement in blood is associated with several drawbacks. It needs a sample of blood, drawn from the body. Even though the equipment has become more sensitive, and therefore requires less blood, the process is associated with pain and the number of tests typically limited to less than 10 per day. It is also known that large variations in measured values can be caused by the measurement procedure.
- the present invention is concerned with a variety of parameters like de-hydration, lactic-acid, and amino-acids in addition to glucose.
- one pressure sensor of the differential type which directly measure the difference between the two chambers, will increase the sensitivity and accuracy by order of magnitudes.
- a piezo-resistive element in which the sensing resistors are “buried” into the silicon, and do therefore not get into contact with the liquid in the reference volumes are used.
- the buried resistors can be part of a Wheatstone bridge.
- FIG. 1 illustrates an example of embodiment of the present invention.
- FIG. 2 illustrates another example of embodiment of the present invention.
- FIG. 3 illustrates another example of embodiment of the present invention.
- FIG. 4 illustrates an arrangement of an embodiment of the present invention.
- FIG. 5 illustrates another example of embodiment of the present invention.
- FIG. 6A illustrates a side view of an example of an embodiment of the present invention.
- FIG. 6B illustrates a top view of the example shown in FIG. 6A .
- the total sensor consists of two main parts.
- the first part is the sensing apparatus, which is placed inside the human (or animal) body.
- the other part is the control unit, which receives the sensor signal, converts it to the concentration of the solute, with the possibility of storing and displaying the real-time as well as average values.
- a change in the glucose concentration in vivo has two effects. One is the direct change in the osmolality of the ISF. The other is a change in fluid composition (without necessary changing the total concentration of osmotic active substances). Both these effects have to be measured, as the body will be inclined to maintain a constant osmolality by slowly adjusting the concentration of the electrolytes.
- Changes in the chemical composition in vivo is a combination of A) Direct changes in the osmolality of the fluid, which are directly reflected by the sensor. B) Changes in fluid composition (without changing the total concentration of osmotic active substances).
- the main difficulty when using osmotic techniques is to obtain an adequate specificity (the ability to distinguish between the different osmotic components).
- FIG. 1 illustrates an example of embodiment according to the present invention.
- a sensor housing 1 made in silicon comprises a sensor 2 which is a pressure transducer or a variable capasitor that will register a change in the pressure caused by a variable flux of water inn or out of the membrane and/or a change in volume hat activates the sensor 2 .
- a charged membrane 3 comprising both anion and cation charges are supported by a perforated support 4 .
- a callibrated fluid 5 is present in the porous substance 6 , where the osmolality is defined by the content of molecules.
- the fluid will normally be water while the solute is salt or for example glucose or other types of molecules.
- a normal condition is when the osmolality is equal on both sides of the membrane.
- the first one is that the osmolality of the body fluid will increase which causes water to be forced out of the sensor which reduces the fluid volume in the sensor.
- the second effect is to change the electrical potential in the membrane due to the charges. This is illustrated with the circuit 7 .
- a normal fluid condition provides a defined voltage over the membrane. When the ion concentration increases the voltage will change according to the negative or positive charges, and the detected difference and the osmolality changes will be proportional to the ion concentration in the fluid, and it will indicate if the registered osmolality is due to glucose or lactates.
- FIG. 2 illustrates another embodiment of the present invention where there are arranged two membranes 2 and 4 on each side of the sensor housing 1 .
- the membrane 2 has a cut-off enabling diffusion of glucose or lactions 7 in a reference fluid 6 , butt hat will cut off larger molecules.
- the membrane 4 has a cur-off that gives an osmotic effect for glucose molecules 8 , butt hat reduces or has no osmotic effect for lactions 7 .
- the cavity above the sensor 5 provides two separate chambers filled with a porous material preferred to be an inert metal, ceramics or plastic that support the membranes from the side that faces the reference chambers. Above each membrane is arranged a stiff perforated plate 3 made of metal, ceramics or plastic.
- FIG. 3 illustrates another embodiment of the present invention.
- the embodiment has the same elements as in the example illustrated in FIG. 2 , but the area of the two membranes 2 and 4 are different.
- FIG. 5 illustrates an example of embodiment of the present invention where the sensor do not provides a calibrated fluid as a reference, but two charged membranes A and B with different charges made of silicon, titan or another biocompatible material.
- the potential between the membranes will be changed and will be proportional to the ion concentration of the body fluid.
- FIGS. 6A and 6B illustrates an arrangement of a power supply, an ASIC circuit and the reference chambers according to the present invention.
- differential measurements are the clue to solve the problem with specificity. Differential measurements make it possible to measure the various diffusion rates (permeability) of the species that contributes to the osmotic pressure. By combining the measurements from different membranes we can therefore track the changes in concentration of the solute in question.
- reference fluid The fluid inside the reference volumes, hereafter called reference fluid, is based on water, with added solutes.
- the type and amount of solutes is chosen to closely resemble the in vivo condition. (This fluid could for instance be Ringer Acetate).
- a specific amount of a non harmful, non toxic, fully water soluble solute with a high molecular weight (>1000 Dalton) is added. This is done to ensure that the hydrostatic pressure inside the reference chambers always is higher than in the surrounding fluid. In this way, the formation of gas bubbles is avoided, which could otherwise cause a serious fail-function of the sensor.
- differential pressure transducers are one of the main features of the present invention. This is done to; A) Compensate for changes in hydrostatic pressure (caused by external air pressure variations, as well as tension in muscles etc.). B) Increase the resolution of the sensing elements, as the membranes of the pressure transducers are only subjected to the difference between the two osmotic pressures. As these differences are small, highly sensitive elements are designed. This increased sensitivity is important also for improving the specificity of the sensor
- the semipermeable membranes are designed such that small molecules ( ⁇ 180 Dalton) and ions to some extent will pass through the membrane.
- concentration of these substances in the reference chambers will thereby to some extent adjust to the interstitial body fluid.
- the sensor can not rely on finding the ideal membranes.
- the clue is membranes that have different properties with respect to the different solutes encountered in vivo.
- the membranes also posses other important properties. These includes
- the “active” part of the membrane (where the osmotic properties are defined) is added as a thin film on top of the silicon substrate.
- This can either be a non-organic material, made for instance by a “Sol-gel” technique.
- the water permeability must be sufficiently high. Minimising the diffusion length and maximising the pore density in the membrane support structure obtain this.
- the senor can easily be adapted to accept commercially available membranes of different types.
- the design of the reference volumes is important to obtain a high accuracy.
- One important factor is to minimise concentration gradients in the reference volume caused by the transport of water (or solutes) across the membrane. This is done by ensuring that the depth of the reference chambers (normal to the semipermeable membrane) is small compared to the square root of the diffusivity times the wanted response time of the element.
- the reference chambers is formed in a material and with an external structure to minimise the volume displacement of the chambers when exposed to changes in hydrostatic pressure. This is important to minimise the amount of water transport through the membrane, which will increase the response time.
- the reference volume is designed such that gas-bubbles are not trapped inside re-entrant cavities. This is obtained by a combination of the geometrical shape and by the choice of materials (avoid hydrophobic materials).
- the diameter of the filling hole has to be sufficient to avoid problems with surface tension induced pressures.
- the filling hole is plugged under liquid, and the system is designed to obtain a minimum of volume change during plugging, to avoid high pressure peeks.
- the osmotic membranes have a sufficient permeability for the low-molecular solutes (ions), filling of solvent (and low molecular weight substances) can be obtained through the osmotic membrane.
- the last method requires that the high molecular weight materials be deposited into the chamber before the membranes are joined to the pressure transducer.
- the actual filling of the “solvent” could also be performed in the body, after implantation. This can be obtained by for instance sputtering onto one or both of the parts constituting the osmotic element, not on the bonding surfaces (sputtering through a mask or Lift-off) prior to bonding.
- the vapour pressure inside the reference volume must be reduced compared to the external liquid (solvent) to facilitate the fling of the chamber. This is obtained by using the vapour pressure depressing effects caused by the addition of a solute in the reference volume (the high molecular weight material).
- the invention make it possible to use silicon microelectronics whereby the sensor can be made very small and be given numerous different geometrical shapes and can thus be implanted with minute surgical operations. But, the sensor can also be produced by conventional machining technology with the only difference that the geometrical shape and size will be different.
- the electrical signal from the pressure transducer is transformed to make it suitable for wire-less transmission to an external receiver unit.
- Both the coding (protocol) and the frequency is chosen to provide data integrity, security and low power consumption.
- Such “radio” transmission systems do partly exist today, and are also under development.
- the energy can either be supplied internally from a battery, or by for instance magnetic induction.
Abstract
Description
-
- Preferably no (or only a small) thermal expansion miss-match with the silicon pressure sensor
- Ease of bonding to the silicon pressure sensor
- Easily defined geometrical properties as well as precisely adaptable displacement
Claims (6)
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
NO20032608A NO317911B1 (en) | 2003-06-10 | 2003-06-10 | Sensor for in vivo paints of osmotic changes |
NO20032608 | 2003-06-10 | ||
PCT/NO2004/000166 WO2004107972A1 (en) | 2003-06-10 | 2004-06-09 | Sensor in vivo measurement of osmotic changes |
Publications (2)
Publication Number | Publication Date |
---|---|
US20060173252A1 US20060173252A1 (en) | 2006-08-03 |
US7276028B2 true US7276028B2 (en) | 2007-10-02 |
Family
ID=27607250
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/559,323 Active 2024-07-27 US7276028B2 (en) | 2003-06-10 | 2004-06-09 | Sensor in vivo measurement of osmotic changes |
Country Status (12)
Country | Link |
---|---|
US (1) | US7276028B2 (en) |
EP (1) | EP1631187B1 (en) |
JP (1) | JP4399455B2 (en) |
CN (1) | CN100475129C (en) |
AT (1) | ATE391453T1 (en) |
CA (1) | CA2527251C (en) |
DE (2) | DE602004012998T2 (en) |
DK (1) | DK1631187T3 (en) |
ES (1) | ES2305805T3 (en) |
HK (1) | HK1087606A1 (en) |
NO (1) | NO317911B1 (en) |
WO (1) | WO2004107972A1 (en) |
Cited By (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20100223981A1 (en) * | 2007-08-20 | 2010-09-09 | Lifecare As | Apparatus and method for measuring augmented osmotic pressure in a reference cavity |
US20100288370A1 (en) * | 2007-08-22 | 2010-11-18 | Osmotex Ag | Textile having water transport and heating capabilities |
US20120022347A1 (en) * | 2009-04-14 | 2012-01-26 | Koninklijke Philips Electronics N.V. | Using muscle tension sensing to locate an analyte measurement site on the skin |
US8287495B2 (en) | 2009-07-30 | 2012-10-16 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8650937B2 (en) | 2008-09-19 | 2014-02-18 | Tandem Diabetes Care, Inc. | Solute concentration measurement device and related methods |
US9555186B2 (en) | 2012-06-05 | 2017-01-31 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US9839378B2 (en) | 2007-02-06 | 2017-12-12 | Medtronic Minimed, Inc. | Optical systems and methods for ratiometric measurement of blood glucose concentration |
CN109813635A (en) * | 2019-01-01 | 2019-05-28 | 中国人民解放军63653部队 | Based on electric field through the device of diffusion method measurement nucleic diffusion coefficient in rock soil medium |
Families Citing this family (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
NO317911B1 (en) | 2003-06-10 | 2004-12-27 | Lifecare As | Sensor for in vivo paints of osmotic changes |
NZ580449A (en) | 2003-09-11 | 2011-06-30 | Theranos Inc | Ingestible medical device with biocompatible polymer coating, device with microarray to interact with disease marker |
US8088097B2 (en) | 2007-11-21 | 2012-01-03 | Glumetrics, Inc. | Use of an equilibrium intravascular sensor to achieve tight glycemic control |
US8738107B2 (en) * | 2007-05-10 | 2014-05-27 | Medtronic Minimed, Inc. | Equilibrium non-consuming fluorescence sensor for real time intravascular glucose measurement |
US8105261B2 (en) | 2007-07-02 | 2012-01-31 | Cardiac Pacemakers, Inc. | Osmotic devices and methods for diuretic therapy |
US7734349B2 (en) * | 2007-07-18 | 2010-06-08 | Cardiac Pacemakers, Inc. | Osmometric heart monitoring device and methods |
WO2011041546A1 (en) | 2009-09-30 | 2011-04-07 | Glumetrics, Inc. | Sensors with thromboresistant coating |
US8467843B2 (en) | 2009-11-04 | 2013-06-18 | Glumetrics, Inc. | Optical sensor configuration for ratiometric correction of blood glucose measurement |
NO343313B1 (en) | 2017-03-15 | 2019-01-28 | Lifecare As | Fluid composition, method for preparing the composition and use |
US10241022B2 (en) * | 2017-03-30 | 2019-03-26 | Intel Corporation | Characterizing a fluid sample based on response of a non-planar structure |
NO20170927A1 (en) | 2017-06-07 | 2018-12-10 | Lifecare As | Interstitial fluid osmotic pressure measuring device system and method |
CN108434551B (en) * | 2018-04-13 | 2021-05-14 | 山东中医药大学 | Dropper with injection filtering function |
Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4385636A (en) * | 1978-05-23 | 1983-05-31 | Cosman Eric R | Telemetric differential pressure sensor with the improvement of a conductive shorted loop tuning element and a resonant circuit |
US4538616A (en) * | 1983-07-25 | 1985-09-03 | Robert Rogoff | Blood sugar level sensing and monitoring transducer |
US4718430A (en) * | 1984-09-22 | 1988-01-12 | Walter Holzer | Procedure and device for the administering of insulin or similar long-term medicaments |
US4773269A (en) | 1986-07-28 | 1988-09-27 | Rosemount Inc. | Media isolated differential pressure sensors |
US5337747A (en) | 1989-10-06 | 1994-08-16 | Frederic Neftel | Implantable device for estimating glucose levels |
US5388449A (en) * | 1993-07-06 | 1995-02-14 | Leveen; Harry H. | Osmolarity sensor |
US6546268B1 (en) | 1999-06-02 | 2003-04-08 | Ball Semiconductor, Inc. | Glucose sensor |
WO2003061475A1 (en) | 2002-01-23 | 2003-07-31 | Danfoss A/S | Method and device for monitoring analyte concentration by use of differential osmotic pressure measurement |
WO2004107972A1 (en) | 2003-06-10 | 2004-12-16 | Lifecare As | Sensor in vivo measurement of osmotic changes |
-
2003
- 2003-06-10 NO NO20032608A patent/NO317911B1/en not_active IP Right Cessation
-
2004
- 2004-06-09 ES ES04748746T patent/ES2305805T3/en active Active
- 2004-06-09 DE DE602004012998T patent/DE602004012998T2/en active Active
- 2004-06-09 US US10/559,323 patent/US7276028B2/en active Active
- 2004-06-09 JP JP2006516997A patent/JP4399455B2/en active Active
- 2004-06-09 DE DE04748746T patent/DE04748746T1/en active Pending
- 2004-06-09 CN CNB2004800225866A patent/CN100475129C/en active Active
- 2004-06-09 CA CA2527251A patent/CA2527251C/en active Active
- 2004-06-09 DK DK04748746T patent/DK1631187T3/en active
- 2004-06-09 WO PCT/NO2004/000166 patent/WO2004107972A1/en active Application Filing
- 2004-06-09 EP EP04748746A patent/EP1631187B1/en active Active
- 2004-06-09 AT AT04748746T patent/ATE391453T1/en not_active IP Right Cessation
-
2006
- 2006-07-18 HK HK06107997A patent/HK1087606A1/en not_active IP Right Cessation
Patent Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4385636A (en) * | 1978-05-23 | 1983-05-31 | Cosman Eric R | Telemetric differential pressure sensor with the improvement of a conductive shorted loop tuning element and a resonant circuit |
US4538616A (en) * | 1983-07-25 | 1985-09-03 | Robert Rogoff | Blood sugar level sensing and monitoring transducer |
US4718430A (en) * | 1984-09-22 | 1988-01-12 | Walter Holzer | Procedure and device for the administering of insulin or similar long-term medicaments |
US4773269A (en) | 1986-07-28 | 1988-09-27 | Rosemount Inc. | Media isolated differential pressure sensors |
US5337747A (en) | 1989-10-06 | 1994-08-16 | Frederic Neftel | Implantable device for estimating glucose levels |
US5388449A (en) * | 1993-07-06 | 1995-02-14 | Leveen; Harry H. | Osmolarity sensor |
US6546268B1 (en) | 1999-06-02 | 2003-04-08 | Ball Semiconductor, Inc. | Glucose sensor |
WO2003061475A1 (en) | 2002-01-23 | 2003-07-31 | Danfoss A/S | Method and device for monitoring analyte concentration by use of differential osmotic pressure measurement |
WO2004107972A1 (en) | 2003-06-10 | 2004-12-16 | Lifecare As | Sensor in vivo measurement of osmotic changes |
Cited By (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9839378B2 (en) | 2007-02-06 | 2017-12-12 | Medtronic Minimed, Inc. | Optical systems and methods for ratiometric measurement of blood glucose concentration |
US20100223981A1 (en) * | 2007-08-20 | 2010-09-09 | Lifecare As | Apparatus and method for measuring augmented osmotic pressure in a reference cavity |
US8539822B2 (en) * | 2007-08-20 | 2013-09-24 | Lifecare As | Apparatus and method for measuring augmented osmotic pressure in a reference cavity |
US20100288370A1 (en) * | 2007-08-22 | 2010-11-18 | Osmotex Ag | Textile having water transport and heating capabilities |
US8481890B2 (en) * | 2007-08-22 | 2013-07-09 | Osmotex Ag | Textile having water transport and heating capabilities |
US9400241B2 (en) | 2008-09-19 | 2016-07-26 | Tandem Diabetes Care, Inc. | Solute concentration measurement device and related methods |
US8650937B2 (en) | 2008-09-19 | 2014-02-18 | Tandem Diabetes Care, Inc. | Solute concentration measurement device and related methods |
US20120022347A1 (en) * | 2009-04-14 | 2012-01-26 | Koninklijke Philips Electronics N.V. | Using muscle tension sensing to locate an analyte measurement site on the skin |
US8758323B2 (en) | 2009-07-30 | 2014-06-24 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8926561B2 (en) | 2009-07-30 | 2015-01-06 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US9211377B2 (en) | 2009-07-30 | 2015-12-15 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8298184B2 (en) | 2009-07-30 | 2012-10-30 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8287495B2 (en) | 2009-07-30 | 2012-10-16 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US11135362B2 (en) | 2009-07-30 | 2021-10-05 | Tandem Diabetes Care, Inc. | Infusion pump systems and methods |
US11285263B2 (en) | 2009-07-30 | 2022-03-29 | Tandem Diabetes Care, Inc. | Infusion pump systems and methods |
US9555186B2 (en) | 2012-06-05 | 2017-01-31 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
CN109813635A (en) * | 2019-01-01 | 2019-05-28 | 中国人民解放军63653部队 | Based on electric field through the device of diffusion method measurement nucleic diffusion coefficient in rock soil medium |
Also Published As
Publication number | Publication date |
---|---|
ES2305805T3 (en) | 2008-11-01 |
JP2006527063A (en) | 2006-11-30 |
CN1838910A (en) | 2006-09-27 |
CN100475129C (en) | 2009-04-08 |
HK1087606A1 (en) | 2006-10-20 |
NO317911B1 (en) | 2004-12-27 |
EP1631187A1 (en) | 2006-03-08 |
JP4399455B2 (en) | 2010-01-13 |
CA2527251A1 (en) | 2004-12-16 |
DE602004012998D1 (en) | 2008-05-21 |
CA2527251C (en) | 2010-03-30 |
NO20032608D0 (en) | 2003-06-10 |
WO2004107972A1 (en) | 2004-12-16 |
US20060173252A1 (en) | 2006-08-03 |
DK1631187T3 (en) | 2008-08-04 |
DE602004012998T2 (en) | 2009-07-30 |
ATE391453T1 (en) | 2008-04-15 |
DE04748746T1 (en) | 2006-10-12 |
EP1631187B1 (en) | 2008-04-09 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7276028B2 (en) | Sensor in vivo measurement of osmotic changes | |
US9163273B2 (en) | Biosensors and methods for making and using them | |
EP0451233B1 (en) | Implantable device for measuring glucose levels | |
US9400233B2 (en) | Sensors for long-term and continuous monitoring of biochemicals | |
Johnson et al. | Design and testing of an impedance-based sensor for monitoring drug delivery | |
NO329905B1 (en) | CO2 sensor | |
Vazquez et al. | Microscopic gel–liquid interfaces supported by hollow microneedle array for voltammetric drug detection | |
Van Den Berg et al. | A micro-volume open liquid-junction reference electrode for pH-ISFETs | |
US8490497B2 (en) | Microelectromechanical (MEMS) pressure transducer | |
Tang et al. | Ultraminiature and flexible sensor based on interior corner flow for direct pressure sensing in biofluids | |
Gutierrez et al. | A subnanowatt microbubble pressure sensor based on electrochemical impedance transduction in a flexible all-parylene package | |
Yee et al. | Miniature liquid junction reference electrode with micromachined silicon cavity | |
Ul Haque et al. | A MEMS fabricated cell electrophysiology biochip for in silico calcium measurements | |
CN112955728A (en) | Porous medium parameter measuring device | |
Huang et al. | A MEMS differential affinity sensor for continuous glucose detection | |
US20200196917A1 (en) | Interstitial fluid osmotic pressure measuring device system and method | |
Siegel et al. | Top-down and bottom-up fabrication techniques for hydrogel based sensing and hormone delivery microdevices | |
Tang et al. | An ultraflexible microbubble blood pressure sensor for interventional treatment | |
Huang et al. | A capacitively based MEMS affinity glucose sensor | |
Prabhakaran et al. | Design and analysis of capacitive MEMS viscometric sensor for CGM | |
Boss et al. | MULTI-ANALYTE DETECTION FOR BIOLOGICAL FLUIDS Towards Continous Monitoring of Glucose, Ionized Calcium and pH using a Viscometric Affinity Biosensor | |
Boss et al. | MULTI-ANALYTE DETECTION FOR BIOLOGICAL FLUIDS |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: LIFECARE AS, NORWAY Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:ELLINGSEN, OLAV;KULSEN, BARD ERIK;KRISTIANSEN, HELGE;REEL/FRAME:017771/0720 Effective date: 20060120 |
|
STCF | Information on status: patent grant |
Free format text: PATENTED CASE |
|
AS | Assignment |
Owner name: LIFECARE A.S., NORWAY Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:OSMOLIFE A.S.;REEL/FRAME:020309/0581 Effective date: 20071130 Owner name: OSMOLIFE AS, NORWAY Free format text: CHANGE OF NAME;ASSIGNOR:LIFECARE AS;REEL/FRAME:020309/0577 Effective date: 20061214 |
|
FEPP | Fee payment procedure |
Free format text: PAYOR NUMBER ASSIGNED (ORIGINAL EVENT CODE: ASPN); ENTITY STATUS OF PATENT OWNER: SMALL ENTITY |
|
FPAY | Fee payment |
Year of fee payment: 4 |
|
FPAY | Fee payment |
Year of fee payment: 8 |
|
MAFP | Maintenance fee payment |
Free format text: PAYMENT OF MAINTENANCE FEE, 12TH YR, SMALL ENTITY (ORIGINAL EVENT CODE: M2553); ENTITY STATUS OF PATENT OWNER: SMALL ENTITY Year of fee payment: 12 |